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Relationship between Electromyogram Spectrum Parameters and the Tension-Time Index during Incremental Exercise in Trained Subjects.

Introduction

The overall activity of the inspiratory muscles can be evaluated by different invasive techniques. First the tension-time diaphragmatic index ([TT.sub.DI]) proposed by Bellemare and Grassino (Bellemare and Grassino, 1982; 1983) assesses the activity of the diaphragm during breathing given by [TT.sub.DI] = [P.sub.DI]/[P.sub.DImax] X Ti/[T.sub.TOT] where [P.sub.DI] is the transdiaphragmatic pressure, [P.sub.DImax] the maximal transdiaphragmatic pressure and [T.sub.I]/[T.sub.TOT] the duty cycle. A more direct measurement is the analysis of the time and frequency contents of the electromyographic signal. Both techniques are invasive and involve the use of gastric and oesophageal balloon and oesophageal electrodes respectively. A simplified non-invasive index obtained from the mouth occlusion pressure ([P.sub.0.1]) is proposed as an alternative method. This non-invasive tension-time index, validated during exercise in healthy subjects, is derived from the equation [T.sub.T0.1] = [P.sub.0.1]/[P.sub.Imax] x [T.sub.I]/[T.sub.TOT], where [P.sub.Imax] is the maximal inspiratory pressure and [T.sub.I]/[T.sub.TOT] is the duty cycle (Hayot et al., 2000).

The efficiency of the respiratory muscle during exercise is much debated in the literature. Although some authors have argued that respiratory muscle performance does not limit maximal incremental exercise tolerance in healthy trained and untrained adults (Coast et al., 1990; Hayot et al., 2000), heavy submaximal exercise has been shown to impair respiratory muscle performance in humans (Johnson et al., 1993; Mador et al., 1993). To the best of our knowledge, no study has drawn the comparison between these two techniques. The present study was aimed to measure [T.sub.T0.1] and surface EMG of inspiratory muscles of trained cyclists during a maximal incremental exercise, not to assess fatigue, but to check if [T.sub.T0.1] could also be a reliable index of the inspiratory muscle activity and recruitment. We reasoned that the [T.sub.T0.1] could also be a reliable index of the inspiratory muscle activity and recruitment. Though the activity of inspiratory accessory muscle is more and more important to the genesis of increased pressures it was not reflected by [EMG.sub.di]. To assess the overall activity of the inspiratory muscle, as the [T.sub.T0.1], we used the surface EMG (SEMG) and the aim of our study was to determine whether tension-time index reflects the inspiratory muscle activity and recruitment.

Methods

Subjects

Eight trained males cyclist took part in this study. The experimental procedures complied with the ethical standards of the 1975 Helsinki Declaration and approval was received from the appropriate local institutional review board. All qualified participants were familiarized to exercise on the cycle ergometer and instructed to avoid exercise, food, and caffeine for at least 2 h prior to exercise testing. All subjects were assigned to a maximal exercise testing session with tension-time index and SEMG measurements. The anthropometric, spirometry and maximal inspiratory pressures are listed in the table 1. The ATS spirometry interpretation workshop only states that subjects should be "never-smokers, free of respiratory symptoms and disease" (Johannessen et al., 2007; Redlich et al., 2014). Subjects not meeting these guidelines were excluded.

Occlusion pressure

[P.sub.0.1] is the maximum pressure developed during a spontaneous respiratory effort during a 100 ms occlusion at the beginning of inspiration (Kera et al., 2013; Whitelaw et al., 1975). Its timing is such that it is not influenced by the conscious response to occlusion. Moreover, as this index is derived from the ventilatory drive it has the advantage of being independent of the mechanical properties of the lung (Kera et al., 2013). [P.sub.0.1] a valid index of neural output was assessed at the level of functional residual capacity (FRC) (Whitelaw et al., 1975). Subjects were asked to breathe quietly, with the nose occluded, through a mouthpiece connected to the pneumotachograph (Fleish Lausanne, Switzerland) with a two-way low- resistance breathing valve (0.9 cm[H.sub.2]Ox[L.sup.-1] s, dead space of 50 ml, model 9340 occlusion valve, Hans Rudolph inc, Kansas City, Missouri, U.S.A). During the exhalation phase of breathing, a balloon was rapidly inflated in the inspiratory limb of the breathing circuit to occlude the subsequent inspiratory flow. It was closed during expiration and automatically opened about 150 ms after the onset of the subsequent inspiration. Mouth occlusion pressure ([P.sub.0.1]) was measured with a differential pressure transducer (Druck, LPM 9000 series, [+ or -] 50 cm[H.sub.2]O, Leicester, England). The balloon was inflated with helium from a small gas cylinder, and the valve was controlled manually with a small switch. The subject was asked to continue to breathe normally despite the occlusions. Throughout manoeuvres mentioned previously the subject wore headphones and listened to music to dampen any noise from the switching device controlling the balloon, and could see neither the occlusion valve nor the operator and therefore, was unable to anticipate the airway occlusion. The Lab view interface (Lab view, National Instruments Corporation, Austin, Texas, U.S.A.) that provided a visual feedback was used to identify the onset of inspiration. At rest, manoeuvres were made until five technically satisfactory and reproducible measurements were obtained (variation <10%) (Kera et al., 2013). The highest score was kept for analysis.

Maximal inspiratory pressure

Maximum inspiratory pressure ([P.sub.Imax]) is the force that respiratory muscles are able to generate during an occlusive manoeuvre at prefixed volume (Hautmann et al., 2000). Maximal inspiratory pressure ([P.sub.Imax]) was measured at the functional residual capacity (FRC) (the effect of variation of muscle length on force development should be minimal near FRC where the isometric force length curve of the diaphragm is nearly flat), with a differential pressure transducer (Druck, LPM 9000 series, [+ or -] 350 cm[H.sub.2]O, Leicester, England) using the technique of Black and Hyatt (1969). All subjects had no previous experience of these manoeuvres. Therefore, great care was taken to fully explain the procedures. This was facilitated using an oscilloscope (Gould Inc., Cleveland, OH) that provided a visual feedback to the subjects during the explanations and during the manoeuvres. Subjects breathed comfortably on the experimental apparatus without the airflow resistor. After a steady-state FRC was attained, the inspiratory and expiratory ports were occluded at the end exhalation with a balloon shutter valve, and the subject was asked to perform a maximal inspiratory effort. The shutter valve opened automatically after five seconds, and the highest inspiratory pressure that was sustained for at least 1 s was taken as the [P.sub.Imax]. Manoeuvres were made until three technically satisfactory and reproducible measurements were obtained (variation <10 %) (Harik-Khan et al., 1998). The highest score was kept for analysis.

Derived Parameters

[T.sub.T0.1] was estimated as ([P.sub.0.1]/[P.sub.Imax] x [T.sub.I]/[T.sub.TOT]). For the [T.sub.T0.1] equation [P.sub.0.1], [P.sub.Imax] and [T.sub.I]/[T.sub.TOT] were assessed at rest and during exercise. [T.sub.T0.1] is an index of the activity of overall inspiratory muscles. High values of [T.sub.T0.1] correspond to high risk of fatigue, as it was shown by Hayot and coworkers (2000).

Surface electromyography (SEMG) measurements

During maximal exercise testing, the SEMG activities were recorded from the diaphragm and intercostal muscles. Bipolar (20mm inter electrode distance) SEMG recording (silver-silver chloride electrodes with 8 mm active diameter; EA224a model, in Vivo Metrics, U.S.A) was employed. Before electrodes applications, the skin was cleaned by abrasion and sponged with an alcohol-ether-acetone mixture to reduce the inter electrode impedance below 2 kQ Electrodes were placed between the 7th and 8th intercostal space, on the right side, 1 cm from the lateral board of the rib cage, and the reference electrode on the wrist.

The myoelectrical activities of respiratory muscles were amplified (differential amplifier) and passed through upper (1kHz) and lower (1Hz) cutt-off filters. Diaphragm electromyography (SEMG) signals recorded by surface electrodes were strongly corrupted by ECG interference. Since ECG signals have large amplitudes and SEMG surface electrodes are positioned adjacent to the heart, SEMG recordings include a large << noise >> ECG component. Spectra of the SEMG and ECG signals overlap in the same frequency range. Therefore, simple elimination of the ECG interference by filtering the SEMG signal fails. it is an effective method to separate an interfering signal from a signal of interest when the two signals have overlapping spectra (Akkiraju and Reddy, 1992). it has been also demonstrated that a substantial degree of separation between signals and noise can be obtained in the wavelet domain. in this work, these two well-known denoising techniques were combined to improve the performance of the decontamination procedure. The adaptive filter coefficients were adjusted using information derived from the wavelet coefficients of the two ANC scheme input signals: reference input (ECG) and primary input (SEMG). The estimated noise component provided by the adaptive filter was sub tracted from the primary input (SEMG) in order to remove the interferences (Figure 1). The SEMG signals were recorded online using acquisition software (Spatol, Divergent, Compiegne, France). The denoised SEMG signal was analysed by using data computing software (Calvise, Divergent, Compiegne, France). The SEMG signals were sampled in 2048 Hz. The software computed a mean power spectrum density (PSD) by calculating the RMS values of eight consecutive spectra obtained from 0.5-s time windows. The mean pSd was defined by 256 points, in the 0-512Hz frequency bands. The mean power frequency MPF was defined as the frequency that divided the PSD into two regions containing equal power. The RMS and MPF of the PSD were computer calculated in real time.

Protocol

Before each exercise test, we measured the occlusion pressure at rest. The subjects comfortably seated, breathing quietly during 2-3 min. After a stable respiratory ratio was attained, the following parameters were determined from an average of 15 s during 5 min: oxygen consumption (V[O.sub.2]), carbon dioxide output VC[O.sub.2], minute ventilation (Ve), tidal volume ([V.sub.T]), breathing frequency (f), inspiratory time (Ti) and expiratory time ([T.sub.E]). Each subject performed at least 10 occlusions at a rate of 2 to 3 per min. Next, the subjects performed maximal inspiratory pressure ([P.sub.Imax]) measurements using the technique of Black and Hyatt (Black and Hyatt, 1969) and then a cycle ergometer (ER 900, Jeager, Germany) and rested for 3 min. This was followed by a 3 min 60 W warm-up period. The workload was then increased in steps of 30 W every 90 s. We have chosen 90 s steps to perform 3 occlusion measurements in the last 45 s. ECG was recorded continuously during maximal exercise testing. The pedalling speed was fixed at 60 rpm throughout the test. Oxygen uptake was determined using an open circuit technique with the CPX system (Medical Graphics Corporation, St. Paul, U.S.A.). The calibration of the flow module was accomplished by introducing a calibrated volume of air at several flow rates with a 3l pump. Expired gas was analysed for oxygen with a zirconium analyser and for carbon dioxide with an infrared analyser. Gas analysers were calibrated before each test using a standard certified commercial gas preparation. The inspiratory airflow, the fraction of expired oxygen (FE[O.sub.2]) and of carbon dioxide (FEC[O.sub.2]) were computer calculated from the last 10 breathing cycles of every minute. Averages were then established for minute ventilation ([V.sub.E], l x min-1 , body temperature pressure saturated [BTPS]), oxygen uptake (V[O.sub.2], l x [min.sup.-1], standard temperature and pressure dry [STPD]), carbon dioxide production (VC[O.sub.2], l x [min.sup.-1] , STPD), respiratory ratio, ventilatory equivalent for oxygen ([V.sub.E]/V[O.sub.2]), and carbon dioxide ([V.sub.E]/VC[O.sub.2]), and breathing frequency. The exercise was considered to be maximal when three of the following criteria were obtained (Edvardsen et al., 2014; Poole et al., 2008): i) levelling off V[O.sub.2] ii) HRmax > 90% theoretical HR max (Hansen et al., 1984) iii) respiratory exchange ratio RER was greater than 1.15 iv) pedal rate < 50 rpm v) volitional exhaustion. Peak V[O.sub.2] was defined as the highest V[O.sub.2] that could be sustained for at least 30 seconds during the last stage of exercise. At the end of the test, each patient had a 2-minute active recovery and a 3-minute passive recovery. Oxygen uptake (V[O.sub.2]), carbon dioxide output, respiratory ratio and parameters such as [T.sub.I], [T.sub.E] (expiratory time), [T.sub.TOT], f (respirator frequency), [V.sub.E], and [V.sub.T] (tidal volume) were continuously measured using the CPX.

Statistical analysis

For statistical treatments, we used the StatView software (Abacus Concepts, Berkeley, California, U.S.A.). All values were expressed as mean and standard deviation ([+ or -] SD). Linear regression analysis was performed using the least squares method. This analysis was carried out using RMS and MPF as dependent variables and [T.sub.T0.1] as an independent variable. The difference between [P.sub.Imax], before and ten minutes after the end of the exercise was tested with paired Student's test. A p<0.05 was considered statically significant.

Results

Mean anthropometric characteristics and spirometrics data and maximal inspiratory pressure at rest in cyclist subjects are presented in Table 1. Gas exchange and breathing pattern parameters at rest and maximal exercise are listed in the Table 2.

Subjects did not show significant decrease in their maximal inspiratory pressure ten minutes after the end of the exercise compared to rest, respectively 126 [+ or -] 39 vs. 120 [+ or -] 22 cm[H.sub.2]O. The tension-time index increased with exercise intensity to reach at maximal effort a mean maximum value of [T.sub.T0.1] = 0.12 (Figure 2). At the same time the root mean square (RMS) and the mean power frequency increased with exerted mechanical power output. RMS profile was normalized with respect to the highest value and MPF profile to the initial value, as follows: [RMS.sub.i] % = ([RM.sub.Si]/[RMS.sub.max]) x 100 and MPF, % = ([MPF.sub.i]/initial MPF) x 100. Results of spectral analysis of SEMG showed homogeneity in RMS and MPF profiles during the maximal exercise between subjects. All showed the same RMS (Figure 5) and MPF kinetics profiles (Figure 4b). Both RMS and MPF increased in all subjects during exercise (respectively Figure 3a and 3b).

We found positive linear correlation between RMS and [T.sub.T0.1] (r = 0.81, p < 0.001; Figure 4).

Discussion

The present study confirms and extends the relationship between inspiratory muscle recruitment by surface EMG and the tension-time index. The main finding of this study was the validation of the noninvasive [T.sub.T0.1] as a good index of inspiratory muscle recruitment.

Inspiratory muscle function can be evaluated by measurement of ([T.sub.T0.1]) the noninvasive tension-time index of the inspiratory muscles (Hayot et al., 2000). The tension-time index of inspiratory muscle constitutes a very good mechanical index of [O.sub.2] consumption of the respiratory muscles over a wide variety of breathing patterns (Field et al., 1984; Hayot et al., 2000). The noninvasive tension-time index [T.sub.T0.1] (Hayot et al., 2000) had never been compared with surface electromyography. Both root mean square and [T.sub.T0.1] increased during incremental exercise, and were strongly correlated. [T.sub.T0.1] seemed to be a good index to monitor inspiratory muscles activation and inspiratory muscle recruitment during exercise.

The time content of the SEMG established the energy and/or the electric power of the signal. it is well established that the root mean square (RMS) is the best index of the relation EMG/strength. The RMS kinetic is dependent on the number and the firing rate of motor units (MU) (De Luca, 1984).

In the present study, the RMS of the inspiratory muscle of the trained subjects increased with the increase of workload. The increase of RMS was continued from the onset to the end of the maximal testing in all subjects (Figure 4a), indicating the recruitment of additional motor units by the muscle in exercise to maintain a sufficient force level to undertake the workload. Since MPF was shown to be a good index to detect muscle fatigue by lowered frequencies (De Luca, 1984; Gerdle et al., 1990; Petrofsky and Lind, 1980), we suggested that it continuous increase, in all subjects (Figure 4b), demonstrated the non-fatigue of inspiratory muscle in cyclists during a maximal incremental exercise. This result was confirmed by the absence of any difference between [P.sub.Imax] before and 10 min after the end of the exercise (126 [+ or -] 39 vs. 120 [+ or -] 22 cm[H.sub.2]O). On the other hand, it is in agreement with previous studies dealing with trained subjects during maximal incremental exercise (Choukroun et al., 1993; Coast et al., 1990).

[T.sub.T0.1] describes the relationship between the force of contraction ([P.sub.0.1]/[P.sub.Imax]) and the duration of contraction (Ti/[T.sub.TOT]). The overall inspiratory muscle activity increased progressively (Figure 2) during exercise which provides adequate ventilation. The increase in RMS was concomitant with the increase of the [T.sub.T0.1] for each subject during the maximal testing (Figure 5). We found a positive correlation between the [T.sub.T0.1] and RMS (r = 0.81, p < 0.001; Figure 4). We proved that the simple [T.sub.T0.1] measured is a good index of inspiratory muscle load. The [T.sub.T0.1] faithfully tracks the EMG activity and hence represents the load on the respiratory system. Even if [T.sub.T0.1] index is a noninvasive method to assess the performance of inspiratory muscles, it seems to be also a good way to be used rather than of SEMG to monitor inspiratory muscle activity and muscle recruitment.

The most important limitation of our study is the relatively small number of subjects included. This is due to the complexity of the protocol. However, the statistically significant positive associations and correlations between [T.sub.T0.1] and the other indices, render our findings even more meaningful.

Conclusion

In summary, the [T.sub.T0.1] has a good correlation with SEMG parameters to evaluate the inspiratory activity of the respiratory system, at rest and during increased ventilatory demand. We propose that [T.sub.T0.1] could be an easy noninvasive and practical way to evaluate the inspiratory muscle recruitment.

Key points

* Overall activity of the inspiratory muscles can be evaluated by different invasive techniques.

* TT0.1 a reliable index of the inspiratory muscle activity and recruitment

* TT0.1 reflects the diaphragmatic activity during incremental exercise in healthy subjects.

Acknowledgements

The authors thank the medical staff of the department of Cardiac Rehabilitation of Cobie's Hospital for their technical assistance. There is no financial conflict of interest between authors.

Received: 23 March 2016 / Accepted: 12 May 2016 / Published (online): 14 August 2018

References

Akkiraju, P. and Reddy, D.C. (1992) Adaptive cancellation technique in processing myoelectric activity of respiratory muscles. IEEE Transactions on Biomedical Engineering 39, 652-625.

Bellemare, F. and Grassino, A. (1982) Effect of pressure and timing of contraction on human diaphragm fatigue. Journal of Applied Physiology 53, 1190-1195.

Bellemare, F. and Grassino, A. (1983) Force reserve of the diaphragm in patients with chronic obstructive pulmonary disease. Journal of Applied Physiology 55, 8-15.

Black, L.F. and Hyatt, R.E. (1969) Maximal respiratory pressures: normal values and relationship to age and sex. American review of respiratory disease 99, 696-702.

Choukroun, M.L., Kays, C., Gioux, M., Techoueyres, P. and Guenard, H. (1993) Respiratory muscle function in trained and untrained adolescents during short-term high intensity exercise. European Journal of Applied Physiology and Occupational Physiology 67, 14-19.

Coast, J.R., Clifford, P.S., Henrich, T.W., Stray-Gundersen, J. and Johnson, R.L., Jr. (1990) Maximal inspiratory pressure following maximal exercise in trained and untrained subjects. Medicine & Science in Sports & Exercise 22, 811-815.

De Luca, C.J. (1984) Myoelectrical manifestations of localized muscular fatigue in humans. Critical Reviews in Biomedical Engineering 11, 251-279.

de Torres, J.P., Talamo, C., Aguirre-Jaime, A., Rassulo, J. and Celli, B. (2003) Electromyographic validation of the mouth pressure-time index: a noninvasive assessment of inspiratory muscle load. Respiratory Medicine 97, 1006-1013.

Edvardsen, E., Hem, E. and Anderssen, S.A. (2014) End criteria for reaching maximal oxygen uptake must be strict and adjusted to sex and age: a cross-sectional study. PLoS One 9, e85276.

Field, S., Sanci, S. and Grassino, A. (1984) Respiratory muscle oxygen consumption estimated by the diaphragm pressure-time index. Journal of applied physiology: respiratory, environmental and exercise physiology 57, 44-51.

Gerdle, B., Eriksson, N.E. and Brundin, L. (1990) The behaviour of the mean power frequency of the surface electromyogram in biceps brachii with increasing force and during fatigue. With special regard to the electrode distance. Electromyography and clinical neurophysiology 30, 483-489.

Hansen, J.E., Sue, D.Y. and Wasserman, K. (1984) Predicted values for clinical exercise testing. American Review of Respiratory Disease 129, S49-55.

Harik-Khan, R.i., Wise, R.A. and Fozard, J.L. (1998) Determinants of maximal inspiratory pressure. The Baltimore Longitudinal Study of Aging. American Journal of Respiratory and Critical Care Medicine 158, 1459-1464.

Hautmann, H., Hefele, S., Schotten, K. and Huber, R.M. (2000) Maximal inspiratory mouth pressures (PiMAX) in healthy subjects--what is the lower limit of normal? Respiratory Medicine 94, 689-693.

Hayot, M., Ramonatxo, M., Matecki, S., Milic-Emili, J. and Prefaut, C. (2000) Noninvasive assessment of inspiratory muscle function during exercise. American Journal of Respiratory and Critical Care Medicine 162, 2201-2207.

Johannessen, A., Omenaas, E.R., Eide, G.E., Bakke, P.S. and Gulsvik, A. (2007) Feasible and simple exclusion criteria for pulmonary reference populations. Thorax 62, 792-798.

Johnson, B.D., Babcock, M.A., Suman, O.E. and Dempsey, J.A. (1993) Exercise-induced diaphragmatic fatigue in healthy humans. Journal of Physiology 460, 385-405.

Kera, T., Aihara, A. and Inomata, T. (2013) Reliability of airway occlusion pressure as an index of respiratory motor output. Respiratory Care 58, 845-849.

Mador, M.J., Magalang, U.J., Rodis, A. and Kufel, T.J. (1993) Diaphragmatic fatigue after exercise in healthy human subjects. American Review of Respiratory Disease 148, 1571-1575.

Petrofsky, J.S. and Lind, A.R. (1980) Frequency analysis of the surface electromyogram during sustained isometric contractions. European Journal of Applied Physiology and Occupational Physiology 43, 173-182.

Poole, D.C., Wilkerson, D.P. and Jones, A.M. (2008) Validity of criteria for establishing maximal O2 uptake during ramp exercise tests. European Journal of Applied Physiology 102, 403-410.

Redlich, C.A., Tarlo, S.M., Hankinson, J.L., Townsend, M.C., Eschenbacher, W.L., Von Essen, S.G., Sigsgaard, T. and Weissman, D.N. (2014) Official American Thoracic Society technical standards: spirometry in the occupational setting. A American Journal of Respiratory and Critical Care Medicine 189, 983-993.

Whitelaw, W.A., Derenne, J.P. and Milic-Emili, J. (1975) Occlusion pressure as a measure of respiratory center output in conscious man. Respiration Physiology 23, 181-199.

Mehdi Chlif (1) ([mail]), David Keochkerian (2), Abdou Temfemo (2), Dominique Choquet (2) and Said Ahmaidi (2)

(1) Tunisian Research Laboratory Sport Performance Optimization, National Center of Medicine and Science in Sports, Tunis, Tunisia; (2) EA 3300 "APERE: Adaptations-Rehabilitation", Picardie Jules Verne University, Sport Science Department, Amiens, F-80025 Cedex, France

AUTHOR BIOGRAPHY

Mehdi CHLIF

Employment

Assistant professor, Department of Biology of Physical Activity, Higher institute of the Sport and the physical education of Sfax, Tunisia

Degree

PhD

Research interests

Exercise testing, cardiopulmonary and muscular testing and training

E-mail: mehdi.chlif@gmail.com

David KEOCHKERIAN

Employment

Department of Rehabilitation of Cobie's Hospital, France

Degree

PhD

Research interests

Exercise testing, cardiopulmonary and muscular testing and training

E-mail: david.keochkerian@gmail.com

Abdou TEMFEMO

Employment

Exercise and Sport Physiology Unit, Faculty of Sciences, and Department of Biological Sciences, Faculty of Medicine and Pharmaceutical Sciences, University of Douala, Douala, Cameroon

Degree

PhD

Research interests

Neuromuscular fatigue, exercise testing, rehabilitation

E-mail: abdou.temfemo@u-picardie.fr

Dominique CHOQUET

Employment

Doctor of Medicine in Cardiology.

Degree

PhD

Research interests

Exercise testing and training in elderly and cardiac patients.

E-mail: domichoquet@gmail.com

Said AHMAIDI

Employment

Head of Research Laboratory EA-3300: APERE "Exercise Physiology and

Rehabilitation".

Degree

PhD

Research interests

Cardiorespiratory and Muscle Exercise Physiology and Rehabilitation.

E-mail: said.ahmaidi@u-picardie.fr

([mail]) Mehdi Chlif, PhD

Research Unit "Evaluation, Sport, Sante", National Center of Medicine and Science in Sports (CNMSS), Bp263, Ave Med Ali Akid, 1004 El Menzah, Tunis, Tunisia

Caption: Figure 1. Primary input (SEMG) filtered. (a) Surface respiratory EMG signal contaminated with ECG and power line interference signals, (b) ECG signal, (c) Cleaned surface respiratory EMG signal.

Caption: Figure 2. The Tension-time index of the inspiratory muscles TT0.1 for all subjects during incremental exercise.

Caption: Figure 3. A) RMS kinetics profiles during incremental exercise. B) MPF kinetics profiles during incremental exercise

Caption: Figure 4. A) Correlation between RMS and TT0.1. B) Correlation between MPF and TT0.1

Caption: Figure 5. Kinetic of RMS and TT0.1 during incremental exercise.
Table 1. Anthropometrics, spirometrics and maximal inspiratory
pressure at rest in cyclists subjects. Values are reported
as mean ([+ or -] SD).

Variables                            % of predicted value

Age (years)               26 (5)
Height (m)              1.77 (.05)
Weight (kg)             69.4 (6.5)
FVC (l)                  5.9 (.3       114 ([+ or -]2)
FEV1 (l)                 4.8 (.4        110([+ or -]5)
FEV1/FVC (%)            81.6 (1.8      108 ([+ or -]2)
PImax (cmH2O), before    126 (39)
PImax (cmH2O), after     120 (22)

FVC = Forced Vital Capacity; FEV1 = Forced expiratory volume in one
second; PImax = maximal inspiratory pressure.

Table 2. Gas exchange and breathing pattern parameters at
rest and maximal exercise in cyclist subjects. Value are
reported as mean ([+ or -]SD).

                                            Rest        Maximal exercise

V[O.sub.2] (ml.[kg.sup.-1].[min.sup.-1])    6.2 (.9)       56.7 (8.6)
VC[O.sub.2] (ml.[min.sup.-1])               372 (87)       4839 (483)
VE (l.[min.sup.-1])                        12.7 (2.6)     151.2 (19.0)
VT (ml)                                    1004 (117)      3290 (220)
P0.1 (cm[H.sub.2]O)                         1.3 (.2)       27.8 (7.0)
TI/TTOT                                     .41 (.02)       .47 (.04)
VT/TI (l.[s.sup.-1])                         .4 (.1)       5.39 (1.0)
f (bpm)                                      12 (3)          48 (10)

V[O.sub.2] = oxygen uptake; VC[O.sub.2] = carbon dioxide output; VE =
minute ventilation; VT = tidal volume; P0.1 = occlusion pressure;
TI-TTOT = mean inspiratory time to total time of the respiratory cycle;
VT-TI = mean inspiratory flow and f = respiratory frequency.
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Title Annotation:Research article
Author:Chlif, Mehdi; Keochkerian, David; Temfemo, Abdou; Choquet, Dominique; Ahmaidi, Said
Publication:Journal of Sports Science and Medicine
Article Type:Report
Date:Sep 1, 2018
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